Device and method for heat-sensitive agent application

ABSTRACT

A method of directing energy to tissue includes the initial steps of determining target tissue location and/or target tissue margins, positioning an ablation device for delivery of energy to target tissue, and introducing a material having a shape into a tissue region to be monitored. The material is adapted to change echogenic properties in response to heat. The method also includes the steps of applying energy to the ablation device, monitoring the material on a monitor, determining an echogenic response of the material, and terminating ablation if it is determined that the echogenic response of the material is outside a predetermined target tissue threshold.

CROSS REFERENCE TO RELATED APPLICATION

The present application claims the benefit of and priority to U.S.Provisional Application Ser. No. 61/708,905, filed on Oct. 2, 2012, theentire contents of which are incorporated herein by reference.

BACKGROUND

1. Technical Field

The present disclosure relates to systems, devices and methods forperforming a medical procedure. More particularly, the presentdisclosure relates to devices and methods for heat-sensitive agent(and/or drug agent) application, electrosurgical systems including thesame, and methods of directing energy to tissue using the same.

2. Discussion of Related Art

Electrosurgery is the application of electricity and/or electromagneticenergy to cut, dissect, ablate, coagulate, cauterize, seal or otherwisetreat biological tissue during a surgical procedure. When electricalenergy and/or electromagnetic energy is introduced to tissue, theenergy-tissue interaction produces excitation of molecules, creatingmolecular motion that results in the generation of heat. Electrosurgeryis typically performed using a handpiece including a surgical instrument(e.g., end effector, ablation probe, or electrode) adapted to transmitenergy to a tissue site during electrosurgical procedures, anelectrosurgical generator operable to output energy, and a cableassembly operatively connecting the surgical instrument to thegenerator.

Treatment of certain diseases requires the destruction of malignanttissue growths, e.g., tumors. Electromagnetic radiation can be used toheat and destroy tumor cells. Treatment may involve inserting ablationprobes into tissues where cancerous tumors have been identified. Oncethe probes are positioned, electromagnetic energy is passed through theprobes into surrounding tissue. The application of ultrasound imaging isone of the cost-effective methods often used for tumor localization andablation device placement.

There are a number of different types of apparatus that can be used toperform ablation procedures. Typically, apparatus for use in ablationprocedures include a power generating source, e.g., a microwave or radiofrequency (RF) electrosurgical generator, that functions as an energysource, and a surgical instrument (e.g., microwave ablation probe havingan antenna assembly) for directing the energy to the target tissue. Thegenerator and surgical instrument are typically operatively coupled by acable assembly having a plurality of conductors for transmitting energyfrom the generator to the instrument, and for communicating control,feedback and identification signals between the instrument and thegenerator.

Using electrosurgical instruments to ablate, seal, cauterize, coagulate,and/or desiccate tissue may result in some degree of thermal injury tosurrounding tissue. For example, electrosurgical desiccation may resultin undesirable tissue damage due to thermal effects, wherein otherwisehealthy tissue surrounding the tissue to which the electrosurgicalenergy is being applied is thermally damaged by an effect known in theart as “thermal spread”. During the occurrence of thermal spread, excessheat from the operative site can be directly conducted to the adjacenttissue and/or the release of steam from the tissue being treated at theoperative site can result in damage to the surrounding tissue. Theduration of the activation of the generator is directly related to theheat produced in the tissue. The greater the heat produced, the more thepotential for thermal spread to adjacent tissues.

Currently available systems and methods for controlling anelectrosurgical generator during electrosurgery may include a clinicianmonitoring and adjusting, as necessary, the amount of energy deliveredto a tissue site through current, voltage, impedance, and/or powermeasurements such that an appropriate tissue effect can be achieved atthe tissue site with minimal collateral damage resulting to adjacenttissue. These systems and/or methods typically require a clinician totranslate the desired tissue effect to a power setting on anelectrosurgical generator and, if necessary, adjust the power setting tocompensate for tissue transformations (e.g., desiccation of tissue)associated with the electrosurgical procedure such that a desired tissueeffect may be achieved.

It can be difficult to determine the size of an ablated zone and/or toassess the margins of ablated tissue. As can be appreciated, limitingthe possibility of thermal spread or the like during an electrosurgicalprocedure reduces the likelihood of unintentional and/or undesirablecollateral damage to surrounding tissue structures which may be adjacentto an intended treatment site. Controlling and/or monitoring the depthof thermal spread during an electrosurgical procedure may aid aclinician in assessing tissue modification and/or transformation duringthe electrosurgical procedure.

Medical imaging has become a significant component in the clinicalsetting and in basic physiology and biology research, e.g., due toenhanced spatial resolution, accuracy and contrast mechanisms that havebeen made widely available. Medical imaging now incorporates a widevariety of modalities that noninvasively capture the structure andfunction of the human body. Such images are acquired and used in manydifferent ways including medical images for diagnosis, staging andtherapeutic management of malignant disease.

Because of their anatomic detail, computed tomography (CT) and magneticresonance imaging (MRI) are suitable for, among other things, evaluatingthe proximity of tumors to local structures. CT and MRI scans producetwo-dimensional (2-D) axial images, or slices, of the body that may beviewed sequentially by radiologists who visualize or extrapolate fromthese views actual three-dimensional (3-D) anatomy.

Medical image processing, analysis and visualization play anincreasingly significant role in disease diagnosis and monitoring aswell as, among other things, surgical planning and monitoring oftherapeutic procedures. Unfortunately, tissue heating and thermal damagedoes not create adequate contrast in ultrasound images to allowdetermination of the size of an ablated zone and assessment of themargins of ablated tissue.

SUMMARY

A continuing need exists for systems, devices and methods forcontrolling and/or monitoring real-time tissue effects to improvepatient safety, reduce risk, and/or improve patient outcomes. There is aneed for intraoperative techniques for ablation margin assessment andfeedback control.

According to an aspect of the present disclosure, a method of directingenergy to tissue is provided. The method includes the initial steps ofdetermining target tissue location and/or target tissue margins,positioning an ablation device for delivery of energy to target tissue,and introducing a material having a shape into a tissue region to bemonitored. The material is adapted to change echogenic properties inresponse to heat. The method also includes the steps of applying energyto the ablation device, monitoring the material on a monitor,determining an echogenic response of the material, and terminatingablation if it is determined that the echogenic response of the materialis outside a predetermined target tissue threshold.

According to another aspect of the present disclosure, a method ofdirecting energy to tissue is provided. The method includes the initialsteps of determining target tissue location and/or target tissuemargins, positioning an energy applicator for delivery of energy totarget tissue, and positioning one or more shaped portions of aheat-sensitive material into tissue. The one or more shaped portions ofthe heat-sensitive material are adapted to change echogenic propertiesin response to heat. The method also includes the steps of transmittingenergy from an electrosurgical power generating source through theenergy applicator to the target tissue, acquiring data representative ofone or more images including data representative of a response of theone or more shaped portions of the heat-sensitive material to the heatgenerated by the energy transmitted to the target tissue, anddetermining at least one operating parameter associated with theelectrosurgical power generating source based at least in part on theresponse of the one or more shaped portions of the heat-sensitivematerial.

In any one of the aspects, the one or more operating parametersassociated with the electrosurgical power generating source may beselected from the group consisting of temperature, impedance, power,current, voltage, mode of operation, and duration of application ofelectromagnetic energy.

Electromagnetic energy is generally classified by increasing energy ordecreasing wavelength into radio waves, microwaves, infrared, visiblelight, ultraviolet, X-rays and gamma-rays. As it is used in thisdescription, “microwave” generally refers to electromagnetic waves inthe frequency range of 300 megahertz (MHz) (3×10⁸ cycles/second) to 300gigahertz (GHz) (3×10¹¹ cycles/second).

As it is used in this description, “ablation procedure” generally refersto any ablation procedure, such as microwave ablation, radio frequency(RF) ablation or microwave ablation assisted resection. As it is used inthis description, “energy applicator” generally refers to any devicethat can be used to transfer energy from a power generating source, suchas a microwave or RF electrosurgical generator, to tissue. As it is usedin this description, “transmission line” generally refers to anytransmission medium that can be used for the propagation of signals fromone point to another. As it is used in this description, “fluid”generally refers to a liquid, a gas or both.

BRIEF DESCRIPTION OF THE DRAWINGS

Objects and features of the presently-disclosed devices forheat-sensitive agent (and/or drug agent) application, electrosurgicalsystems including the same, and methods of directing energy to tissueusing the same will become apparent to those of ordinary skill in theart when descriptions of various embodiments thereof are read withreference to the accompanying drawings, of which:

FIG. 1 is a schematic diagram of an electrosurgical system, such as amonopolar electrosurgical system, according to an embodiment of thepresent disclosure;

FIG. 2 is a schematic diagram of another embodiment of anelectrosurgical system according to the present disclosure;

FIG. 3 is an enlarged, perspective view of an injection device adaptedfor the delivery of a material, e.g., a heat-sensitive agent, intotissue, the device including a housing and a plunger assembly, accordingto an embodiment of the present disclosure;

FIG. 4 is an enlarged, cross-sectional view of the energy applicator ofFIG. 2 positioned for delivery of energy to a target tissue, shown withthe injection device of FIG. 3 having a material, e.g., a heat-sensitiveagent, disposed within the housing according to an embodiment of thepresent disclosure;

FIG. 5 is an enlarged, cross-sectional view of an energy applicatorarray positioned for delivery of energy to a target tissue, shown withtwo injection devices of FIG. 3 having a material, e.g., aheat-sensitive agent, disposed within the housing according to anembodiment of the present disclosure;

FIG. 6 is an enlarged, cross-sectional view of an RF ablation devicepositioned for delivery of energy to a target tissue, shown with theinjection device of FIG. 3 having a material, e.g., a heat-sensitiveagent, disposed within the housing according to an embodiment of thepresent disclosure;

FIG. 7 is an enlarged, cross-sectional view of the injection device ofFIG. 3 shown disposed, in part, within a target tissue, e.g., positionedrelative to the RF ablation device and/or in relation to the targettissue of FIG. 6, shown with the housing and the plunger assembly of theinjection device disposed in a first configuration according to anembodiment of the present disclosure;

FIG. 8A is an enlarged, cross-sectional view of the injection device ofFIG. 3 shown disposed, in part, within the target tissue of FIG. 7,shown with the housing and the plunger assembly disposed in a secondconfiguration, upon the delivery of a linearly-shaped portion of amaterial, e.g., a heat-sensitive agent, into the target tissue,according to an embodiment of the present disclosure;

FIG. 8B is an enlarged, cross-sectional view of the injection device ofFIG. 3 shown disposed, in part, within the target tissue of FIG. 7,shown with the housing and the plunger assembly disposed in a secondconfiguration, upon the delivery of a curvilinear-shaped portion of amaterial, e.g., a heat-sensitive agent, into the target tissue,according to an embodiment of the present disclosure;

FIG. 9 is an enlarged, cross-sectional view of the target tissue of FIG.8A, shown with the linear-shaped portion of the material, e.g., aheat-sensitive agent, positioned relative to the RF ablation deviceand/or in relation to the target tissue, shown with injection deviceafter withdrawal thereof from the target tissue according to anembodiment of the present disclosure;

FIG. 10 is a diagrammatic representation of a tissue region, includingnormal tissue to a region of thermal damage, shown with the energydelivery device of FIG. 7 and a linearly-shaped portion of material,e.g., a heat-sensitive agent, according to an embodiment of the presentdisclosure;

FIG. 11 is a schematic diagram of an electrosurgical system shown withthe injection device of FIG. 3, shown with the energy applicator arrayof FIG. 5 positioned for the delivery of energy to target tissue,according to an embodiment of the present disclosure;

FIG. 12 is a flowchart illustrating a method of directing energy totissue in accordance with an embodiment of the present disclosure; and

FIG. 13 is a flowchart illustrating a method of directing energy totissue in accordance with another embodiment of the present disclosure.

DETAILED DESCRIPTION

Hereinafter, embodiments of the presently-disclosed device and methodfor heat-sensitive agent application, electrosurgical system includingthe same, and method of directing energy to tissue using the same aredescribed with reference to the accompanying drawings. Like referencenumerals may refer to similar or identical elements throughout thedescription of the figures. As shown in the drawings and as used in thisdescription, and as is traditional when referring to relativepositioning on an object, the term “proximal” refers to that portion ofthe device, or component thereof, closer to the user and the term“distal” refers to that portion of the device, or component thereof,farther from the user.

This description may use the phrases “in an embodiment,” “inembodiments,” “in some embodiments,” or “in other embodiments,” whichmay each refer to one or more of the same or different embodiments inaccordance with the present disclosure.

Various embodiments of the present disclosure provide electrosurgicalsystems and instruments suitable for sealing, cauterizing,coagulating/desiccating and/or cutting vessels and vascular tissue,ablating tissue, or otherwise modifying a tissue or organ of a patient,wherein the use of the presently-disclosed heat-sensitive agent, whichis adapted to be visually observable and/or ascertainable in anultrasound image (or other medical image), may provide feedback to allowthe surgeon to selectively position the energy applicator in tissueduring a procedure, and/or may allow the surgeon to adjust, asnecessary, of the amount of energy delivered to tissue to facilitateeffective execution of a procedure, e.g., an ablation procedure.

Various embodiments of the presently-disclosed electrosurgical systemsand instruments use heat-distribution information provided byapplication of the presently-disclosed heat-sensitive agent. Inaccordance with embodiments of the present disclosure, a configurationof one or more heat-sensitive agents and/or drug agents(s) provides awell-organized shape (e.g., linear shape and/or curved shape) and/orpattern (e.g., regular, geometric pattern) adapted to be visuallyobservable and/or ascertainable in an ultrasound image (or other medicalimage), e.g., to allow assessment of ablation margins and/or the rate ofablation and/or desiccation of tissue. Embodiments may be implementedusing energy at RF or microwave frequencies or at other frequencies.

In accordance with embodiments of the present disclosure, one or moreoperating parameters of an electrosurgical power generating source areadjusted and/or controlled based on the heat-distribution informationprovided by the presently-disclosed heat-sensitive agent, e.g., tomaintain a proper ablation rate, or to determine when tissue has beencompletely desiccated and/or the procedure has been completed.

During a procedure, such as an ablation or other heat treatmentprocedure, heat may not be uniformly distributed, such as at interfaceshaving different tissue properties, and accurate monitoring of, theablation may require multi-point measurements of temperaturedistribution. The presently-disclosed heat-sensitive agent may beinserted into or placed adjacent to tissue in a variety ofconfigurations, e.g., to allow visual assessment of ablation margins, orto allow the surgeon to determine the rate of ablation and/or when theprocedure has been completed, and/or to trigger safety procedures and/orcontrols, e.g., controls that reduce power level and/or shut off thepower delivery to the energy applicator.

Various embodiments of the presently-disclosed electrosurgical systemsuse heat-distribution information provided by the presently-disclosedheat-sensitive agent, which is adapted to be visually observable and/orascertainable in an ultrasound image (or other medical image), totrigger safety procedures and/or controls, e.g., controls that reducepower level and/or shuts off the power delivery to the energyapplicator, e.g., based on the tissue ablation rate and/or assessment ofthe ablation margins.

FIG. 1 schematically illustrates a monopolar electrosurgical system(shown generally as 1) configured to selectively apply electrosurgicalenergy to target tissue of a patient P. Electrosurgical system 1generally includes a handpiece 2 coupled via a transmission line 4 to anelectrosurgical power generating source 20. Handpiece 2 includes asurgical instrument 14 having one or more electrodes for treating tissueof the patient P (e.g., electrosurgical pencil, electrosurgical cuttingprobe, ablation electrode(s), etc.). In some embodiments, as shown inFIG. 1, the handpiece 2 includes a control assembly 30. When theelectrosurgical energy is applied, the energy travels from the activeelectrode, to the surgical site, through the patient P and to a returnelectrode 6 (e.g., a plate positioned on the patient's thigh or back).

Electrosurgical energy is supplied to the instrument 14 by theelectrosurgical power generating source 20. Power generating source 20may be any generator suitable for use with electrosurgical devices togenerate energy having a controllable frequency and power level, and maybe configured to provide various frequencies of electromagnetic energy.Power generating source 20 may be configured to operate in a variety ofmodes, such as ablation, monopolar and bipolar cutting, coagulation, andother modes. Control assembly 30 may include a variety of mechanismsadapted to generate signals for adjusting and/or controlling one or moreoperating parameters (e.g., temperature, impedance, power, current,voltage, mode of operation, and/or duration of application ofelectromagnetic energy) of the electrosurgical power generating source20.

The instrument 14 is electrically-coupled via a transmission line, e.g.,supply line 4, to an active terminal 23 of the electrosurgical powergenerating source 20, allowing the instrument 14 to coagulate, ablateand/or otherwise treat tissue. The energy is returned to theelectrosurgical power generating source 20 through the return electrode6 via a transmission line, e.g., return line 8, which is connected to areturn terminal 22 of the power generating source 20. In someembodiments, the active terminal 23 and the return terminal 22 may beconfigured to interface with plugs (not shown) associated with theinstrument 14 and the return electrode 6, respectively, e.g., disposedat the ends of the supply line 4 and the return line 8, respectively.

The system 1 may include a plurality of return electrodes 6 that arearranged to minimize the chances of tissue damage by maximizing theoverall contact area with the patient P. The power generating source 20and the return electrode 6 may additionally, or alternatively, beconfigured for monitoring so-called “tissue-to-patient” contact toensure that sufficient contact exists therebetween to further minimizechances of tissue damage. The active electrode may be used to operate ina liquid environment, wherein the tissue is submerged in an electrolytesolution.

FIG. 2 schematically illustrates an electrosurgical system (showngenerally as 10) including an energy applicator or probe 100. Probe 100generally includes an antenna assembly 12, and may include a feedline(or shaft) 110 coupled to the antenna assembly 12. Located at the distalend of the antenna assembly 12 is an end cap or tapered portion 120,which may terminate in a sharp tip 123 to allow for insertion intotissue with minimal resistance. Feedline 110 may include a coaxialcable, which may be semi-rigid or flexible. A transmission line 15 maybe provided to electrically couple the feedline 110 to anelectrosurgical power generating source 28, e.g., a microwave or RFelectrosurgical generator.

Feedline 110 may be cooled by fluid, e.g., saline or water, to improvepower handling, and may include a stainless steel catheter. Transmissionline 15 may additionally, or alternatively, provide a conduit (notshown) configured to provide coolant from a coolant source 18 to theprobe 100. In some embodiments, as shown in FIG. 2, the feedline 110 iscoupled via a transmission line 15 to a connector 17, which furtheroperably connects the probe 100 to the electrosurgical power generatingsource 28. Power generating source 28 may be any generator suitable foruse with electrosurgical devices, and may be configured to providevarious frequencies of energy.

During microwave ablation, e.g., using the electrosurgical system 10,the probe 100 is inserted into or placed adjacent to tissue andmicrowave energy is supplied thereto. One or more linear-shaped (and/orcurve-shaped) portions of a heat-sensitive agent or agents, which aredescribed in more detail later in this description, may be positionedrelative to the probe 100 (and/or relative to a target tissue). Probe100 may be placed percutaneously or atop tissue, e.g., usingconventional surgical techniques by surgical staff. A plurality ofprobes 100 may be placed in variously arranged configurations tosubstantially simultaneously ablate a target tissue, making fasterprocedures possible. Ablation volume is correlated with antenna design,antenna performance, number of energy applicators used simultaneously,ablation time and wattage, and tissue characteristics, e.g., tissueimpedance.

FIG. 3 shows an injection device (shown generally as 300) adapted fordelivery of a heat-sensitive agent or agents, a drug agent or agents, orcombinations thereof, into tissue according to an embodiment of thepresent disclosure. In some embodiments, the injection device 300 may beadapted to deliver a linearly-shaped portion and/or a curvilinear-shapedportion of a material, which may include heat-sensitive agent(s) and/ordrug agent(s).

Injection device 300 generally includes a housing 310 and a plungerassembly 314. Housing 310 includes an elongated tubular body 312defining a proximal end 311 and a distal end 315. Body 312 may have anysuitable dimensions, e.g., length. Body 312 defines a chamber or fluidreservoir 318 therein. In some embodiments, as shown in FIG. 3, thehousing 310 includes a slanted opening 320 disposed at the distal end315 of the body 312. In some embodiments, as shown in FIG. 3, a flange322 is disposed at the proximal end 311 of the body 312.

Body 312 may include any suitable material. In some embodiments, thebody 312 is made of plastic, e.g., transparent polypropylene. Body 312may be constructed of nearly any polymeric or glass material. In someembodiments, the body 312, or portion thereof, and/or the plungerassembly 314, or portion thereof, may be formed of a flexible materialor materials, e.g., to allow delivery of one or more curvilinear-shaped(and/or linearly-shaped) portions of a heat-sensitive agent or agents(and/or medicament) into tissue.

Plunger assembly 314 is adapted to be mountable in the fluid reservoir318 of the body 312 and moveable with respect to the housing 310.Plunger assembly 314 includes a plunger rod 324, and may include aflange 321 disposed at the proximal end of the plunger rod 324. Plungerrod 324 may include a plurality of vanes extending outwardly from acenter longitudinal axis and extending at substantially right angles toeach other. Plunger rod 324 may include any suitable material, e.g.,plastic.

Fluid reservoir 318 may be configured to contain a predetermined volumeof a heat-sensitive agent or agents, a drug agent or agents, orcombinations thereof. In some embodiments, the fluid reservoir 318 mayhave an internal volume in the range of about 0.5 ml (milliliters) toabout 100 ml.

In some embodiments, as shown in FIG. 3, the plunger assembly 314includes a sealing member 326. Sealing member 326 is configured to beslideably received within the fluid reservoir 318 of the body 312, andmay include one or more annular ribs 330 that sealingly engage an innerwall of the body 312 defining reservoir 318. Sealing member 326 mayinclude any suitable material. In some embodiments, the sealing member326 is formed from an elastomeric material.

Although the housing 310 shown in FIG. 3 has a generally tubular shape,it is to be understood that housing embodiments may have any suitablecross-sectional configuration. In some embodiments, the housing 310 mayinclude a body 312 having a rectangular, triangular, or polygonal shape.In some embodiments, the housing 310 may include an opening 320 that isrectangular, triangular, octagonal or oval shaped.

In some embodiments, the injection device 300 may be configured as asingle-use, auto-disable injection device. In alternative embodimentsnot shown, the injection device may include a driver mechanism, e.g.,compressed gas, for imparting movement to the plunger assembly 314.

In FIGS. 4 through 6, the injection device 300 of FIG. 3 is shownprovided with a material 340 disposed within the fluid reservoir 318 ofthe body 312, prior to placement of the injection device 300 into atarget tissue “T”. In FIGS. 4 through 6, the housing 310 and the plungerassembly 314 of the injection device 300 are shown disposed in a firstconfiguration, e.g., wherein the plunger assembly 314 is disposed in aretracted position.

Material 340 disposed within the fluid reservoir 318 may include one ormore heat-sensitive agents, e.g., adapted to change echogenic propertiesin response to heat generated as a result of energy transmitted to thetarget tissue “T”. The material 340 may exhibit change in its materialproperties and/or echogenic properties in response to received heatabove a certain threshold value. The heat-sensitive agent's response toheat may be reversible, e.g., echogenic and/or material propertiesreturn to non-heated configuration when cooled down. The heat-sensitiveagent's response to heat may be non-reversible, e.g., medium remainsmodified and/or transformed after heat is dissipated. In someembodiments, the material 340 may additionally, or alternatively,include one or more drug agents.

In FIG. 4, the energy applicator 100 of FIG. 2 is shown positioned forthe delivery of energy to target tissue “T”, and the injection device300 is shown located outside of the target tissue “T”, e.g., positionedfor insertion thereinto. Although a single injection device 300 is shownin FIG. 4, it is to be understood that any suitable number of injectiondevices 300 may be used, e.g., to provide a well-organized shape (e.g.,linear shape and/or curved shape) and/or pattern (e.g., regular,geometric pattern) of a heat-sensitive agent or agents and/or a drugagent or drug agents, which may be visually observable and/orascertainable in an ultrasound image (or other medical image).

In FIG. 5, an energy applicator array 50, which is described later inthis description, is shown positioned for the delivery of energy to atarget tissue “T”, and two injection devices 300 are shown locatedoutside of the target tissue “T”, e.g., positioned for insertionthereinto.

In FIG. 6, an RF ablation device 600 is shown positioned for delivery ofenergy to a target tissue “T”, and an injection device 300 is locatedoutside of the target tissue “T”, e.g., positioned for insertionthereinto. For ease of explanation and understanding, a single injectiondevice 300 is described with respect to FIGS. 6 through 9; however, anysuitable number of the injection devices 300 may be used. A variety ofmedical imaging modalities, e.g., computed tomography (CT) scan orultrasound, may be used to guide the RF ablation device 600 and/orinjection device 300 into the area of tissue “T” to be treated.

In FIG. 7, the injection device 300 of FIG. 3, provided with material340 disposed within the fluid reservoir 318, is shown disposed, in part,within the target tissue “T”, e.g., positioned relative to the RFablation device 600 and/or in relation to the target tissue “T” of FIG.6, prior to delivery of the material 340 into the target tissue “T”.

In FIG. 8A, the injection device of FIG. 7 is shown disposed, in part,within the target tissue, shown with the housing 310 and the plungerassembly 314 disposed in a second configuration, e.g., wherein theplunger assembly 314 is disposed in an advanced position, upon thedelivery of a linear-shaped volume of the material 340, e.g., inproximity to the RF ablation device 600.

In FIG. 8B the injection device of FIG. 7 is shown disposed, in part,within the target tissue, shown with the housing 310 and the plungerassembly 314 disposed in a second configuration, e.g., wherein theplunger assembly 314 is disposed in an advanced position, upon thedelivery of a curvilinear-shaped volume of the material 345, e.g., inproximity to the RF ablation device 600.

FIG. 9 is an enlarged, cross-sectional view of the injection device ofFIG. 3, after the removal of the injection device from the target tissueof FIG. 8A, shown with the linear-shaped portion of the heat-sensitiveagent disposed within the target tissue according to an embodiment ofthe present disclosure. In some embodiments, the housing 310 is movedproximally to dispense the linear-shaped volume of the material 340 fromwithin the fluid reservoir 318 into the target tissue “T”. In someembodiments, as shown in FIG. 9, wherein a flange 322 is disposed at theproximal end of the body 312 and a flange 321 is disposed at theproximal end of the plunger rod 324, the injection device 300 may beadapted to fully dispense the material 340 from within the fluidreservoir 318 when the flange 322 associated with the body 312 isbrought into contact with the flange 321 associated with the plunger rod324.

The visual assistance provided by the utilization of thepresently-disclosed material 340 configured as a well-organized shape(e.g., linear shape and/or curved shape) and/or pattern (e.g., regular,geometric pattern) by providing heat-distribution information on adisplay device may allow the surgeon to selectively position the energyapplicator (e.g., probe 100 shown in FIG. 4, energy applicator array 50shown in FIGS. 5 and 11, or RF ablation device 600 shown in FIGS. 6-9)in tissue, and/or may allow the surgeon to monitor and adjust, asnecessary, the amount of energy delivered to tissue, such as tofacilitate effective execution of a procedure, e.g., an ablationprocedure.

FIG. 10 is a diagrammatic representation of a region tissue of “T” shownwith a material 1040 disposed in proximity to the RF ablation device600. Material 1040 is similar to the material 340 shown in FIG. 9 andfurther description thereof is omitted in the interests of brevity.Although, in the illustrative example shown in FIG. 10, the tissue “T”includes first and second zones of thermal damage 1001 and 1002,respectively, it is to be understood that any number of zones of thermaldamage may result from the ablation or other heat-treatment procedure.

As shown in FIG. 10, in response to ablation or other heat-treatmentprocedure, a portion 1028 of the material 1040 exhibits change inmaterial properties and/or echogenic properties, as compared to otherportions of the material 1040 adjacent thereto. In alternativeembodiments not shown, one or more portions of the material 1040, e.g.,portions disposed within the second zone 1002, may additionally, oralternatively, exhibit change in material properties and/or echogenicproperties, e.g., depending on the material properties of the material1040 and/or the change in temperature by a certain amount in the secondzone 1002.

FIG. 11 schematically illustrates an electrosurgical system (showngenerally as 500) according to an embodiment of the present disclosurethat includes an electromagnetic energy delivery device or energyapplicator array 50 positioned for the delivery of energy to a targettissue “T”. Energy applicator array 50 may include one or more energyapplicators or probes.

In some embodiments, as shown in FIG. 11, the electrosurgical system 500includes two material 340 portions, e.g., positioned relative to theenergy applicator array 50 and/or in relation to the target tissue “T”.It is to be understood that any suitable number of the injection device300 may be used. The relative positioning of the material 340 portionsmay be varied from the configuration depicted in FIG. 10.

In the embodiment shown in FIG. 10, the energy applicator array 50includes three probes 51, 52 and 53 having different lengths andarranged substantially parallel to each other. The probes may havesimilar or different diameters, may extend to equal or differentlengths, and may have a distal end with a tapered tip. In someembodiments, the probe(s) may be provided with a coolant chamber, andmay be integrally associated with a hub (e.g., hub 534 shown in FIG. 10)that provides electrical and/or coolant connections to the probe(s).Additionally, or alternatively, the probe(s) may include coolant inflowand outflow ports to facilitate the flow of coolant into, and out of,the coolant chamber.

Probes 51, 52 and 53 generally include a radiating section “R1”, “R2”and “R3”, respectively, operably connected by a feedline (or shaft) 51a, 52 a and 53 a, respectively, to an electrosurgical power generatingsource 516, e.g., a microwave or RF electrosurgical generator. In someembodiments, the power generating source 516 is configured to providemicrowave energy at an operational frequency from about 300 MHz to about10 GHz. Power generating source 516 may be configured to provide variousfrequencies of electromagnetic energy.

Transmission lines 510, 511 and 512 may be provided to electricallycouple the feedlines 51 a, 52 a and 53 a, respectively, to theelectrosurgical power generating source 516. Located at the distal endof each probe 51, 52 and 53 is a tip portion 51 b, 52 b and 53 b,respectively, which may be configured to be inserted into an organ “OR”of a human body or any other body tissue. Tip portion 51 b, 52 b and 53b may terminate in a sharp tip to allow for insertion into tissue withminimal resistance. The shape, size and number of probes of the energyapplicator array 50 may be varied from the configuration depicted inFIG. 10.

Electrosurgical system 500 according to embodiments of the presentdisclosure includes a user interface 550. User interface 550 may includea display device 521, such as without limitation a flat panel graphicLCD (liquid crystal display), adapted to visually display one or moreuser interface elements (e.g., 523, 524 and 525 shown in FIG. 10). In anembodiment, the display device 521 includes touchscreen capability,e.g., the ability to receive user input through direct physicalinteraction with the display device 521, e.g., by contacting the displaypanel of the display device 521 with a stylus or fingertip.

User interface 550 may additionally, or alternatively, include one ormore controls 522 that may include without limitation a switch (e.g.,pushbutton switch, toggle switch, slide switch) and/or a continuousactuator (e.g., rotary or linear potentiometer, rotary or linearencoder). In an embodiment, a control 522 has a dedicated function,e.g., display contrast, power on/off, and the like. Control 522 may alsohave a function that may vary in accordance with an operational mode ofthe electrosurgical system 500. A user interface element (e.g., 523shown in FIG. 10) may be provided to indicate the function of thecontrol 522.

As shown in FIG. 10, the electrosurgical system 500 may include areference electrode 519 (also referred to herein as a “return”electrode). Return electrode 519 may be electrically coupled via atransmission line 520 to the power generating source 516. During aprocedure, the return electrode 519 may be positioned in contact withthe skin of the patient or a surface of the organ “OR”. When the surgeonactivates the energy applicator array 50, the return electrode 519 andthe transmission line 520 may serve as a return current path for thecurrent flowing from the power generating source 516 through the probes51, 52 and 53.

During microwave ablation, e.g., using the electrosurgical system 500,the energy applicator array “E” is inserted into or placed adjacent totissue and microwave energy is supplied thereto. Ultrasound or computedtomography (CT) guidance may be used to accurately guide the energyapplicator array 50 into the area of tissue to be treated. A clinicianmay pre-determine the length of time that microwave energy is to beapplied. Application duration may depend on a variety of factors such asenergy applicator design, number of energy applicators usedsimultaneously, tumor size and location, and whether the tumor was asecondary or primary cancer. The duration of microwave energyapplication using the energy applicator array 50 may depend on theprogress of the heat distribution within the tissue area that is to bedestroyed and/or the surrounding tissue.

FIG. 10 shows a target tissue including ablation target tissuerepresented in sectional view by the solid line “T”. It may be desirableto ablate the target tissue “T” by fully engulfing the target tissue “T”in a volume of lethal heat elevation. Target tissue “T” may be, forexample, a tumor that has been detected by a medical imaging system 570.

Medical imaging system 570, according to various embodiments, includesone or more image acquisition devices (e.g., scanner 515 shown in FIG.10) of any suitable imaging modality. Medical imaging system 570 mayadditionally, or alternatively, include a medical imager (not shown)operable to form a visible representation of the image based on theinput pixel data. Medical imaging system 570 may include acomputer-readable storage medium such as an internal memory unit 576,which may include an internal memory card and removable memory, capableof storing image data representative of an ultrasound image (and/orimages from other modalities) received from the scanner 515. In someembodiments, the medical imaging system 570 may be a multi-modal imagingsystem capable of scanning using different modalities. Medical imagingsystem 570, according to embodiments of the present disclosure, mayinclude any device capable of generating digital data representing ananatomical region of interest.

Image data representative of one or more images may be communicatedbetween the medical imaging system 570 and a processor unit 526. Medicalimaging system 570 and the processor unit 526 may utilize wiredcommunication and/or wireless communication. Processor unit 526 mayinclude any type of computing device, computational circuit, or any typeof processor or processing circuit capable of executing a series ofinstructions that are stored in a computer-readable storage medium (notshown), which may be any device or medium that can store code and/ordata. Processor unit 526 may be adapted to run an operating systemplatform and application programs. Processor unit 526 may receive userinputs from a keyboard (not shown), a pointing device 527, e.g., amouse, joystick or trackball, and/or other devicecommunicatively-coupled to the processor unit 526.

As shown in FIG. 10, a scanner 515 of any suitable imaging modality maybe disposed in contact with the organ “OR” to provide image data. As anillustrative example, the two dashed lines 515A in FIG. 10 bound aregion for examination by the scanner 515, e.g., a real-time ultrasonicscanner.

In FIG. 10, the dashed line 558 surrounding the target tissue “T”represents the ablation isotherm in a sectional view through the organ“OR”. Such an ablation isotherm may be that of the surface achievingpossible temperatures of approximately 50° C. or greater. The shape andsize of the ablation isotherm volume, as illustrated by the dashed line558, may be influenced by a variety of factors including theconfiguration of the energy applicator array 50, the geometry of theradiating sections “R1”, “R2” and “R3”, cooling of the probes 51, 52 and53, ablation time and wattage, and tissue characteristics.

Processor unit 526 may be connected to one or more display devices(e.g., 521 shown in FIG. 10) for displaying output from the processorunit 26, which may be used by the clinician to visualize the targettissue “T”, the ablation isotherm volume 558, and/or the material 340 inreal-time, or near real-time, during a procedure, e.g., an ablationprocedure.

In some embodiments, real-time data and/or near real-time data acquiredfrom the medical imaging system 570 that includes heat-distributioninformation, e.g., data representative of one or more regions of thematerial 340 during an ablation procedure, may be outputted from theprocessor unit 526 to one or more display devices. Processor unit 526 isadapted to analyze image data including heat-distribution information todetermine one or more parameters associated with the energy applicatorarray 50 and/or one or more parameters associated with theelectrosurgical power generating source 516 e.g., based on the tissueablation rate and/or assessment of the ablation margins.

Electrosurgical system 500 may include a library 580 including aplurality of material 340 profiles or overlays 582 ₁-582 _(n). As it isused in this description, “library” generally refers to any repository,databank, database, cache, storage unit and the like. Each of theoverlays 582 ₁-582 _(n) may include a thermal profile that ischaracteristic of and/or specific to particular material 340configurations, e.g., exposure time and/or the change in temperature bya certain amount.

Library 580 according to embodiments of the present disclosure mayinclude a database 584 that is configured to store and retrieve energyapplicator data, e.g., parameters associated with one or more energyapplicators (e.g., 51, 52 and 53 shown in FIG. 10) and/or one or moreenergy applicator arrays (e.g., 50 shown in FIG. 10) and/or parametersassociated with material 340. Images and/or non-graphical data stored inthe library 580, and/or retrievable from a PACS database (not shown),may be used to configure the electrosurgical system 500 and/or controloperations thereof. For example, heat-distribution information, e.g.,data representative of material 340 and/or regions associated therewithduring an ablation procedure, according to embodiments of the presentdisclosure, may be used as a feedback tool to control an instrument'sand/or clinician's motion, e.g., to allow clinicians to avoid ablatingcertain structures, such as large vessels, healthy organs or vitalmembrane barriers.

Hereinafter, methods of directing energy to tissue are described withreference to FIGS. 12 and 13. It is to be understood that the steps ofthe methods provided herein may be performed in combination and in adifferent order than presented herein without departing from the scopeof the disclosure.

FIG. 12 is a flowchart illustrating a method of directing energy totissue according to an embodiment of the present disclosure. In step1210, tumor “T” location and/or tumor “T” margins are determined. Thetarget tissue location and target tissue margins may be determined byusing medical imaging. Any suitable medical imaging techniques may beused, e.g., ultrasound, magnetic resonance imaging (MRI), or computedtomography (CT) imaging.

In step 1220, an ablation device 600 is inserted into tissue “T”.Ultrasound guidance may be used to guide the ablation device 600 intothe area of tissue “T” to be treated. The ablation device 600 isoperably associated with an electrosurgical power generating source 516.

In step 1230, a material 340 having a shape is introduced into a tissueregion “T” to be monitored. The material 340 is adapted to changeechogenic properties in response to heat. The material 340 may includeone or more heat-sensitive agents. In some embodiments, the material 340may include heat-sensitive microbubbles, e.g., a core of liquidperfluorocarbon (PFC) compound and a shell of biodegradable polylactic-co-glycolic acid (PLGA). The material 340 may include one or moredrug agents. In some embodiments, the material 340 may include drugagents, e.g., chemotherapy drugs, encased in heat-sensitivemicrobubbles.

In step 1240, energy from the electrosurgical power generating source516 is applied to the ablation device 600. The electrosurgical powergenerating source 516 may be capable of generating energy at RF ormicrowave frequencies or at other frequencies.

In step 1250, the material 340 is monitored on a monitor 521. In someembodiments, monitoring the material 340, in step 1250, includescontinuing the ablation while one or more portions of the material 340which changed echogenic properties in response to heat (e.g., portion1028 shown in FIG. 10) are displayed on the monitor 521.

In step 1260, an echogenic response of the material 340 is determined.In some embodiments, determining the echogenic response of the material340, in step 1260, includes determining whether one or more portions ofthe material 340, which changed echogenic properties in response toheat, displayed on the monitor 521 are larger than the target tissuemargins determined in step 1210.

If it is determined, in step 1260, that the echogenic response of thematerial 340 is outside a predetermined target tissue threshold (e.g.,one or more portions of the material 340 which changed echogenicproperties in response to heat are larger than the target tissue marginsdetermined in step 1210) then, ablation is terminated, in step 1270.Otherwise, if it is determined, in step 1260, that the echogenicresponse of the material 340 is below a predetermined target tissuethreshold (e.g., one or more portions of the material 340 which changedechogenic properties in response to heat are not larger than the targettissue margins), then repeat step 1250.

FIG. 13 is a flowchart illustrating a method of directing energy totissue according to an embodiment of the present disclosure. In step1310, target tissue (e.g., tumor) “T” location and/or target tissue “T”margins are determined, e.g., by using medical imaging.

In step 1320, an energy applicator 600 is positioned for delivery ofenergy to target tissue “T”. The energy applicator may be inserteddirectly into tissue “T”, inserted through a lumen, e.g., a vein, needleor catheter, placed into the body during surgery by a clinician, orpositioned in the body by other suitable methods. Ultrasound guidancemay be used to guide the energy applicator 600 into the area of tissue“T” to be treated. The energy applicator 600 is operably associated withan electrosurgical power generating source 516.

In step 1330, one or more shaped portions of a heat-sensitive material340 are positioned into tissue “T”. The heat-sensitive material 340 isadapted to change echogenic properties in response to heat. In someembodiments, the heat-sensitive material 340 may include heat-sensitivemicrobubbles. In some embodiments, the heat-sensitive material 340 mayinclude one or more drug agents.

In step 1340, energy from the electrosurgical power generating source516 is transmitted through the energy applicator 600 to the targettissue “T”. The electrosurgical power generating source 516 may becapable of generating energy at RF or microwave frequencies or at otherfrequencies.

In step 1350, data representative of one or more images including datarepresentative of a response of one or more shaped portions of theheat-sensitive material to the heat generated by the energy transmittedto the target tissue is acquired.

In step 1360, one or more operating parameters associated with theelectrosurgical power generating source 516 are determined based atleast in part on response of one or more shaped portions of theheat-sensitive material to the heat generated by the energy transmittedto the target tissue. Some examples of operating parameters associatedwith an electrosurgical power generating source 516 that may bedetermined include temperature, impedance, power, current, voltage, modeof operation, and duration of application of electromagnetic energy.

In some embodiments, safety procedures and/or controls, e.g., controlsthat reduce power level and/or shut off the power delivery to the energyapplicator, may be triggered based on the tissue ablation rate and/orassessment of the ablation margins. In some embodiments, a processorunit 526 configured to generate one or more electrical signals forcontrolling one or more operating parameters associated with anelectrosurgical power generating source 516 may be adapted to reducepower level and/or shut off the power delivery based on the tissueablation rate and/or the proximity of the margins of ablated tissue tothe target tissue margins.

The above-described injection device for heat-sensitive agent (and/ordrug agent) application, electrosurgical devices and systems, andmethods of directing energy to target tissue may be suitable for variousopen and endoscopic surgical procedures.

The above-described heat-sensitive agent may be inserted into or placedadjacent to tissue in a variety of configurations, e.g., to allow visualassessment of ablation margins, or to allow the surgeon to determine therate of ablation and/or when the procedure has been completed, and/or totrigger safety procedures and/or controls, e.g., controls that reducepower level and/or shuts off the power delivery to the energyapplicator. The above-described injection device may be adapted todeliver a linearly-shaped portion and/or a curvilinear-shaped portion ofa material, e.g., including a heat-sensitive agent or agents, a drugagent or agents, or combinations thereof.

The use of the above-described heat-sensitive agent, which is adapted tobe visually observable and/or ascertainable in an ultrasound image (orother medical image), may provide feedback to allow the surgeon toselectively position the energy applicator in tissue during a procedure,and/or may allow the surgeon to adjust, as necessary, of the amount ofenergy delivered to tissue to facilitate effective execution of aprocedure, e.g., an ablation procedure.

In the above-described embodiments, one or more operating parameters ofan electrosurgical power generating source may be adjusted and/orcontrolled based on the heat-distribution information provided by thepresently-disclosed heat-sensitive agent, e.g., to maintain a properablation rate, or to determine when tissue has been completelydesiccated and/or the procedure has been completed.

Although embodiments have been described in detail with reference to theaccompanying drawings for the purpose of illustration and description,it is to be understood that the inventive processes and apparatus arenot to be construed as limited thereby. It will be apparent to those ofordinary skill in the art that various modifications to the foregoingembodiments may be made without departing from the scope of thedisclosure.

What is claimed is:
 1. A method of directing energy to tissue,comprising: introducing a material having a shape into the tissue, thematerial possessing an echogenic property which changes in response toheat; applying energy to a tissue target within the tissue using anablation device; measuring an echogenic property value representing theechogenic property of the material as the echogenic property valuechanges in response to heat generated from the application of energy;determining whether the echogenic property value surpasses apredetermined threshold; and terminating the application of energy ifthe echogenic property value surpasses the predetermined threshold. 2.The method of directing energy to tissue of claim 1, wherein the tissuetarget and the predetermined threshold are determined by using medicalimaging.
 3. The method of directing energy to tissue of claim 1, whereinthe material includes at least one heat-sensitive agent.
 4. The methodof directing energy to tissue of claim 1, wherein the shape of thematerial is linear.
 5. The method of directing energy to tissue of claim1, wherein the shape of the material is curvilinear.
 6. The method ofdirecting energy to tissue of claim 1, wherein the material isintroduced into the tissue using an injection device.
 7. The method ofdirecting energy to tissue of claim 6, wherein the injection device isadapted to deliver a linearly-shaped portion of the material.
 8. Themethod of directing energy to tissue of claim 6, wherein the injectiondevice is adapted to deliver a curvilinear-shaped portion of thematerial.
 9. A method of directing energy to tissue, comprising:positioning at least one shaped portion of a heat-sensitive materialinto the tissue, the at least one shaped portion of the heat-sensitivematerial possessing an echogenic property which changes in response toheat; transmitting energy from an electrosurgical power generatingsource through an energy applicator to a tissue target within thetissue; acquiring data representative of the echogenic property of theat least one portion of the heat-sensitive material as the echogenicproperty changes in response to heat generated by the energy transmittedto the tissue target; and adjusting at least one operating parameter ofthe electrosurgical power generating source based at least in part onthe acquired data.
 10. The method of directing energy to tissue of claim9, wherein the shape of the material is linear.
 11. The method ofdirecting energy to tissue of claim 9, wherein the shape of the materialis curvilinear.
 12. The method of directing energy to tissue of claim 9,wherein the at least one operating parameter associated with theelectrosurgical power generating source is selected from the groupconsisting of temperature, impedance, power, current, voltage, mode ofoperation, and duration of application of electromagnetic energy. 13.The method of directing energy to tissue of claim 9, wherein theheat-sensitive material is introduced into the tissue using an injectiondevice.
 14. The method of directing energy to tissue of claim 13,wherein the injection device is adapted to deliver a linearly-shapedportion of the heat-sensitive material.
 15. The method of directingenergy to tissue of claim 13, wherein the injection device is adapted todeliver a curvilinear-shaped portion of the heat-sensitive material.